US4645506A - Hip joint endoprosthesis with a stem to be anchored in the femur - Google Patents
Hip joint endoprosthesis with a stem to be anchored in the femur Download PDFInfo
- Publication number
- US4645506A US4645506A US06/623,785 US62378584A US4645506A US 4645506 A US4645506 A US 4645506A US 62378584 A US62378584 A US 62378584A US 4645506 A US4645506 A US 4645506A
- Authority
- US
- United States
- Prior art keywords
- main part
- stem
- wedge
- femur
- wedge pieces
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/32—Joints for the hip
- A61F2/36—Femoral heads ; Femoral endoprostheses
- A61F2/3662—Femoral shafts
- A61F2/367—Proximal or metaphyseal parts of shafts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/30721—Accessories
- A61F2/30734—Modular inserts, sleeves or augments, e.g. placed on proximal part of stem for fixation purposes or wedges for bridging a bone defect
Definitions
- the invention relates to a hip joint endoprosthesis with a downward-tapering stem which is to be anchored in the femur and which is composed of a main part connected to the condyle head and of a wedge piece which is movably guided longitudinally along the main part by means of cooperating guide surfaces and has an outer surface formed for promoting adhesion to the bone tissue.
- the wedge piece is provided on the lateral side of the main part of the stem.
- the main part of the stem, carrying the condyle head is first knocked into the bone.
- the wedge piece is knocked in while firmly holding the main part of the stem, the wedge shape of the wedge piece effecting jamming of the stem in the bone, without altering the height position of the main part of the stem in the bone.
- the stem becomes loose, for example due to unphysiological loading or due to ageing phenomena, this can be corrected by knocking the wedge piece further in at a later date during a re-operation.
- this prosthesis it is envisaged with this prosthesis that the main part of the stem assumes and retains a predetermined height relative to the bone and only the wedge action of the wedge piece is utilized by knocking it in for jamming the prosthesis in the bone tube.
- the known prosthesis does not exclude the possibility that the prosthesis becomes loose due to widening of the bone receiving the stem, and a reoperation is certainly necessary in order to eliminate the loosening, by knocking the wedge piece further.
- the object is achieved according to the invention when a plurality of wedge pieces is provided on stem sides facing away from one another and the guide surfaces, converging in the manner of a wedge, are formed to produce an adhesive force which is lower than that of the outer surfaces of the wedge pieces.
- the prosthesis according to the invention differs in principle from the known prosthesis in that the wedge pieces as a rule have a height in the bone, which is fixed once and for all by the operation, whilst the main part of the stem carrying the condyle head is displaceable in the longitudinal direction, in fact automatically due to the natural load which tends to push the main part of the stem further into the bone, between the wedge pieces. Any widening of the bone tube is in this way automatically compensated by an expansion of the wedge pieces with corresponding lowering of the main part of the prosthesis stem.
- the self-adjusting effect of the prosthesis according to the invention is made possible by the fact that the adhesion of the outer surfaces of the wedge pieces to the bone tissue is greater than the adhesion which acts in the cooperating guide surfaces of the main part of the stem and of the wedge pieces.
- An expert is familiar with many possibilities of forming the surface of a prosthesis stem in such a way that adhesion to the bone tissue is promoted, for example by elevations and recesses, surface porosity and perforations into which the bone tissue grows.
- the effect of the invention is tied to the wedge-shaped design of the main part of the stem between the guide surfaces.
- a wedge-shaped design of the wedge pieces is advantageous but not absolutely necessary for this purpose. Rather, it is conceivable that the guide surfaces provided on the wedge pieces run parallel to the outer surfaces thereof in longitudinal section or that the wedge pieces even taper from the distal end to the proximal end, so that the wedge angle effective on the guide surfaces is greater than the natural wedge angle of the medullary canal, widening in the proximal direction, of the femur.
- peripheral surface of the prosthesis stem interacting with the bone tissue, in the upper section thereof to be formed exclusively by the wedge pieces, it is in general more advantageous when, in addition to the wedge pieces, the main part of the prosthesis stem also participates in the formation of the peripheral surface.
- the anchoring forces are, entirely or for a substantial part, transmitted by the surface of the main part of the stem to the bone, so that a wedging movement can take place only when the surface of the main part of the prosthesis stem looses contact with the bone tissue, due to widening of the bone tube, and thus sinks more deeply into the medullary cavity, until the arrangement obtains a hold again as a result of expansion of the wedge pieces.
- a plurality of ribs integral with the stem project from the main part of the stem to the peripheral surface and the wedge pieces are arranged in the interspaces between the ribs.
- the stem advantageously also has a surface structure which is formed to promote adhesion relative to the bone tissue, and, according to a further feature of the invention, even the surface, interacting with the bone tissue, of the main part of the stem can be sized to be adequate for transmitting, by itself, the load.
- the intended effect is that not every strong load on the prosthesis leads to a relative movement of the prosthesis stem in relation to the wedge pieces and the bone tissue. Rather, it is the aim to allow this correction movement to take place only when the bond between the main part of the prosthesis stem and the bone tissue deteriorates.
- This bond can make a contribution to ensuring that the correction movement does not take place traumatically as a sudden fracture phenomenon under a peak load, but is a continuous rearrangement process, in which there is an equilibrium between the forces transmitted by the wedge pieces and the forces transmitted directly from the main part to the bone tissue.
- the wedge angle is smaller than the angle of friction so that, on the one hand, the desired expansion of the wedge pieces for the purpose of compensating a widening of the medullary canal can take place as a result of a load on the prosthesis and, on the other hand, the elastic resilient tendency of the bone tissue cannot lead to the opposite relative movement, which otherwise could entail continuous "pumping" of the arrangement.
- One means for preventing such a continuous alternating movement is to design the cooperating guide surfaces for intensive friction. Only those forces which exceed the frictional force can then cause a relative movement.
- these are each composed of a surface of large wedge angle (angle between this surface and the longitudinal direction of the stem) and a further surface which, with the longitudinal direction of the stem, encloses an angle which is very small, zero or negative (an angle opening downwards).
- the loading forces acting in the longitudinal direction of the stem are thus transmitted via the step surfaces of large wedge angle and, at the same time, the wedge pieces are subjected to an expanding force which is equal to the quotient of the loading forces divided by the tangent of the wedge angle.
- a relative movement then takes place only when the expanding forces become larger than those forces of the bone tissue which counteract the expansion, in the case of an extension by the radial height of a step.
- the expanding force to be absorbed by the bone tissue can be limited by selecting a large wedge angle.
- suitable sizing of the radial step height (measured transversely to the direction of the stem), that degree of medullary canal widening is determined at which a correction jump of the prosthesis parts is to take place in each case.
- the wedge angle and the step height are advantageously sized such that the step height is not larger, or not substantially larger, than the extension of the bone tissue to be expected, on the basis of the wedge angle, under maximum loading.
- the invention presupposes that the prosthesis stem is inserted without cement or with very little cement.
- FIG. 1 shows a side view of a hip joint-femur stem prosthesis
- FIG. 2 shows a cross-section through the stem along the line II--II in FIG. 1,
- FIG. 3 shows a longitudinal section on a larger scale along the line III--III in FIG. 2, in particular with a different design of the guide surfaces on the left-hand and right-hand sides of the center line,
- FIG. 4 shows a partial side view in the direction of projection perpendicular to that in FIG. 1, and
- FIG. 5 shows a stepped design of the guide surfaces.
- the prosthesis consists of the stem 1, the collar 2 which may be exchangeable, the neck 3 of the head and the condyle head 4.
- the stem 1 is shaped conventionally, in such a way that its surface can substantially be in contact with the hard cortex layer of the femur bone.
- ribs 8 which extend in the longitudinal direction of the stem and are rigidly joined to the main part 7, start from the main part 7.
- Three such ribs 8 of cross-sectionally parallel arrangement are provided in each case on the front and rear of the stem. Two ribs are arranged on the inside and one rib is arranged on the outside.
- the ridges of the ribs 8, that is to say those facing outwards, are provided with teeth 9, so that they can be more securely anchored in the bone tissue.
- Other surface shapes which ensure good bonding to the bone tissue can also take the place of the teeth.
- the interspace between two ribs 8 joined to the main part 7 there is in each case an interspace of constant width, which forms in each case a guide for a wedge piece 10 which is movable in the longitudinal direction of the stem between the ribs fixed to the stem and is supported by its guide surface 12 on the bottom 11, forming the guide surfaces, of the interspace between the ribs.
- On its rear surface it has teeth 13 for more secure anchorage in the bone tissue, or it has an alternative surface shape.
- the serration 9 of the ribs rigidly joined to the main part 7 is made in the form of saw teeth in such a way that it offers a resistance to a sinking relative movement which is less than that of the serration 13 of the movable stem parts. However, this is not absolutely necessary.
- the distance between mutually opposite guide surfaces 11 on the different sides of the main part increases from the bottom upwards. This means that they form wedge surfaces, by means of which the wedge pieces 10 are urged outwards when the stem sinks deeper into the medullary cavity and are thus forced into stronger adhesion to the bone tissue and therefore do not share this sinking movement. It can be seen in the longitudinal section of FIG. 4 that the wedge angle 14 enclosed by the guide surfaces 11 with the longitudinal direction of the stem is very small. This means that the wedge pieces 10 virtually do not participate in the transmission of the longitudinal forces from the stem to the bone.
- FIG. 4 shows, in the left-hand half, the smooth version of the pair of guide surfaces 11, 12 and, on the right-hand side, a serrated version which is intended to prevent alternating longitudinal forces from causing varying displacements between the fixed and movable parts of the prosthesis, as long as the displacements remain below a certain threshold.
- FIG. 5 shows a stepped version of the guide surfaces 11 and 12, each step being composed of a surface 15 of large wedge angle 16 and of another surface 17 which extends approximately parallel to the longitudinal direction 18 of the shaft. It is possible to give different shapes to the various pairs of guide surfaces on one and the same prosthesis. However, identical shaping of all the guide surfaces is preferred.
- a rib rigidly joined to the main part of the stem is provided instead of a movable wedge piece, because, in that area, tensile forces are to be transmitted rather than compressive forces.
Landscapes
- Health & Medical Sciences (AREA)
- Orthopedic Medicine & Surgery (AREA)
- Cardiology (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Transplantation (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Vascular Medicine (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Prostheses (AREA)
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE3323131 | 1983-06-27 | ||
DE19833323131 DE3323131A1 (de) | 1983-06-27 | 1983-06-27 | Endoprothese mit einem im knochen zu verankernden schaft |
Publications (1)
Publication Number | Publication Date |
---|---|
US4645506A true US4645506A (en) | 1987-02-24 |
Family
ID=6202514
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US06/623,785 Expired - Lifetime US4645506A (en) | 1983-06-27 | 1984-06-22 | Hip joint endoprosthesis with a stem to be anchored in the femur |
Country Status (4)
Country | Link |
---|---|
US (1) | US4645506A (de) |
EP (1) | EP0131178B1 (de) |
AT (1) | ATE38320T1 (de) |
DE (2) | DE3323131A1 (de) |
Cited By (25)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4840633A (en) * | 1987-01-03 | 1989-06-20 | Manfred Kallabis | Cementless endoprosthesis |
US4842606A (en) * | 1986-03-15 | 1989-06-27 | Mecron Medizinische Produkte Gmbh | Bone implant |
US4936863A (en) * | 1988-05-13 | 1990-06-26 | Hofmann Aaron A | Hip prosthesis |
US4944759A (en) * | 1986-01-21 | 1990-07-31 | Joint Medical Products Corporation | Porous-coated artificial joints |
US4979958A (en) * | 1988-09-29 | 1990-12-25 | Aisin Seiki Kabushiki Kaisha | Artificial stem for femur of coxa |
US5002580A (en) * | 1988-10-07 | 1991-03-26 | Pfizer Hospital Products Group, Inc. | Prosthetic device and method of implantation |
US5062854A (en) * | 1988-10-07 | 1991-11-05 | Pfizer Hospital Products Group | Prosthetic device and method of implantation |
US5089004A (en) * | 1988-01-19 | 1992-02-18 | Osteonics Corp. | Prosthetic implant procedure and femoral broach therefor |
US5258035A (en) * | 1992-05-29 | 1993-11-02 | Intermedics Orthopedics, Inc. | Femoral prosthesis with wedge having opposed tapers |
WO1994015551A1 (en) * | 1993-01-06 | 1994-07-21 | Smith & Nephew Richards, Inc. | Modular humeral component system |
US5483036A (en) * | 1993-10-28 | 1996-01-09 | Sandia Corporation | Method of automatic measurement and focus of an electron beam and apparatus therefor |
US5755811A (en) * | 1995-08-25 | 1998-05-26 | Zimmer, Inc. | Prosthetic implant with fins |
US5755810A (en) * | 1996-11-13 | 1998-05-26 | Cunningham; Robert A. | Hip implant prosthesis |
US5961555A (en) * | 1998-03-17 | 1999-10-05 | Huebner; Randall J. | Modular shoulder prosthesis |
US6368352B1 (en) | 1995-06-08 | 2002-04-09 | Depuy Orthopaedics, Inc. | Large taper modular shoulder prosthesis |
US6494913B1 (en) | 1998-03-17 | 2002-12-17 | Acumed, Inc. | Shoulder prosthesis |
US20040158329A1 (en) * | 2003-02-10 | 2004-08-12 | Waldemar Link (Gmbh & Co.) | Hip joint prosthesis with shaft inserted into femur |
KR100468866B1 (ko) * | 2001-09-10 | 2005-01-29 | 삼성테크윈 주식회사 | 인공 고관절용 무시멘트형 스템 |
US20050075735A1 (en) * | 2000-04-10 | 2005-04-07 | Berelsman Brian K. | Method and apparatus for adjusting height and angle for a radial head |
US20050165493A1 (en) * | 2004-01-22 | 2005-07-28 | Ries Michael D. | Femoral hip prosthesis and method of implantation |
US20080114461A1 (en) * | 2006-11-13 | 2008-05-15 | Howmedica Osteonics Corp. | Modular humeral head |
WO2010051576A1 (en) * | 2008-11-05 | 2010-05-14 | Wui Chung | A femoral hip prosthesis |
US20100241236A1 (en) * | 2000-04-10 | 2010-09-23 | Biomet Manufacturing Corp. | Modular Radial Head Prosthesis |
US20110190900A1 (en) * | 2004-08-06 | 2011-08-04 | Waldemar Link Gmbh & Co. Kg | Hip-joint prosthesis with a shaft to be inserted into the femur |
US8535382B2 (en) | 2000-04-10 | 2013-09-17 | Biomet Manufacturing, Llc | Modular radial head prostheses |
Families Citing this family (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR2579453B1 (fr) * | 1985-03-27 | 1991-06-28 | Epinette Jean Alain | Composant femoral de prothese de hanche, non cimente |
GB2178320B (en) * | 1985-07-29 | 1989-07-19 | Finsbury | Hip implant |
CH667199A5 (de) * | 1985-08-30 | 1988-09-30 | Sulzer Ag | Geradschaft aus metall fuer eine femurkopfprothese. |
US4714470A (en) * | 1986-02-19 | 1987-12-22 | Zimmer, Inc. | Grooved prosthetic implant |
US4795472A (en) * | 1987-01-28 | 1989-01-03 | Zimmer, Inc. | Prosthesis with enhanced surface finish |
CH675962A5 (de) * | 1988-10-04 | 1990-11-30 | Hermann Ag W | |
FR2638351A1 (fr) * | 1988-11-02 | 1990-05-04 | Jose Adrey | Prothese femorale de hanche |
CH680110A5 (de) * | 1989-11-16 | 1992-06-30 | Sulzer Ag | |
ATE146068T1 (de) * | 1992-02-10 | 1996-12-15 | Sulzer Orthopaedie Ag | Gerader blattartiger schaft für eine endoprothese |
FR2703583B1 (fr) * | 1993-04-07 | 1995-06-09 | Medinov Sa | Implant femoral pour prothese de hanche. |
Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE85147C (de) * | ||||
FR817525A (fr) * | 1936-02-15 | 1937-09-04 | Savoisienne Const Elec | Perfectionnement aux enroulements auxiliaires en triangle pour transformateurs |
FR1278359A (fr) * | 1961-01-13 | 1961-12-08 | Maison Drapier | Perfectionnement aux prothèses fémorales |
FR2419717A1 (fr) * | 1978-03-17 | 1979-10-12 | Medizinska Akad | Prothese totale de hanche |
DE2839092A1 (de) * | 1978-09-08 | 1980-03-20 | Hans Dr Reimer | Endoprothese fuer hueft-, knie- oder winkelgelenke |
EP0041591A1 (de) * | 1980-05-09 | 1981-12-16 | Protek AG | Gelenkendoprothese und Scheibenkörper als Drehsicherung |
Family Cites Families (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB817525A (en) * | 1956-10-05 | 1959-07-29 | Maison Drapier Van Steenbruggh | Improvements relating to pegs for pinning long bones through the medullary canal |
DE7235643U (de) * | 1972-09-28 | 1974-06-27 | Fischer A | Hüftgelenkkopfprothese |
DE2726297A1 (de) * | 1977-06-10 | 1978-12-21 | Hans Dr Reimer | Endoprothese fuer hueft-, knie- oder winkelgelenke |
CH652911A5 (de) * | 1982-01-29 | 1985-12-13 | Sulzer Ag | Gerader, blattartiger schaft fuer eine gelenkendoprothese. |
DE8212788U1 (de) * | 1982-05-03 | 1985-09-26 | Waldemar Link Gmbh & Co, 2000 Hamburg | Knochenenimplantat, insbesondere femorale Hüftgelenkprothese |
US4457301A (en) * | 1982-06-18 | 1984-07-03 | Howmedica Inc. | Intramedullary fixation device |
CH658185A5 (de) * | 1983-02-10 | 1986-10-31 | Sulzer Ag | Gerader, blattartiger schaft fuer eine gelenkendoprothese. |
-
1983
- 1983-06-27 DE DE19833323131 patent/DE3323131A1/de not_active Withdrawn
-
1984
- 1984-06-18 EP EP84106965A patent/EP0131178B1/de not_active Expired
- 1984-06-18 AT AT84106965T patent/ATE38320T1/de not_active IP Right Cessation
- 1984-06-18 DE DE8484106965T patent/DE3474906D1/de not_active Expired
- 1984-06-22 US US06/623,785 patent/US4645506A/en not_active Expired - Lifetime
Patent Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE85147C (de) * | ||||
FR817525A (fr) * | 1936-02-15 | 1937-09-04 | Savoisienne Const Elec | Perfectionnement aux enroulements auxiliaires en triangle pour transformateurs |
FR1278359A (fr) * | 1961-01-13 | 1961-12-08 | Maison Drapier | Perfectionnement aux prothèses fémorales |
FR2419717A1 (fr) * | 1978-03-17 | 1979-10-12 | Medizinska Akad | Prothese totale de hanche |
DE2839092A1 (de) * | 1978-09-08 | 1980-03-20 | Hans Dr Reimer | Endoprothese fuer hueft-, knie- oder winkelgelenke |
EP0041591A1 (de) * | 1980-05-09 | 1981-12-16 | Protek AG | Gelenkendoprothese und Scheibenkörper als Drehsicherung |
Cited By (62)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4944759A (en) * | 1986-01-21 | 1990-07-31 | Joint Medical Products Corporation | Porous-coated artificial joints |
US4842606A (en) * | 1986-03-15 | 1989-06-27 | Mecron Medizinische Produkte Gmbh | Bone implant |
US4840633A (en) * | 1987-01-03 | 1989-06-20 | Manfred Kallabis | Cementless endoprosthesis |
US5089004A (en) * | 1988-01-19 | 1992-02-18 | Osteonics Corp. | Prosthetic implant procedure and femoral broach therefor |
US4936863A (en) * | 1988-05-13 | 1990-06-26 | Hofmann Aaron A | Hip prosthesis |
US4979958A (en) * | 1988-09-29 | 1990-12-25 | Aisin Seiki Kabushiki Kaisha | Artificial stem for femur of coxa |
US5062854A (en) * | 1988-10-07 | 1991-11-05 | Pfizer Hospital Products Group | Prosthetic device and method of implantation |
US5002580A (en) * | 1988-10-07 | 1991-03-26 | Pfizer Hospital Products Group, Inc. | Prosthetic device and method of implantation |
US5258035A (en) * | 1992-05-29 | 1993-11-02 | Intermedics Orthopedics, Inc. | Femoral prosthesis with wedge having opposed tapers |
US5480452A (en) * | 1992-05-29 | 1996-01-02 | Intermedics Orthopedics, Inc. | Femoral prosthesis with wedge having opposed tapers |
WO1994015551A1 (en) * | 1993-01-06 | 1994-07-21 | Smith & Nephew Richards, Inc. | Modular humeral component system |
US5489309A (en) * | 1993-01-06 | 1996-02-06 | Smith & Nephew Richards Inc. | Modular humeral component system |
US5483036A (en) * | 1993-10-28 | 1996-01-09 | Sandia Corporation | Method of automatic measurement and focus of an electron beam and apparatus therefor |
US20020095215A1 (en) * | 1995-06-08 | 2002-07-18 | Camino Thomas S. | Large taper modular shoulder prosthesis |
US6368352B1 (en) | 1995-06-08 | 2002-04-09 | Depuy Orthopaedics, Inc. | Large taper modular shoulder prosthesis |
US7238208B2 (en) | 1995-06-08 | 2007-07-03 | Depuy Products, Inc. | Large taper modular shoulder prosthesis |
US5755811A (en) * | 1995-08-25 | 1998-05-26 | Zimmer, Inc. | Prosthetic implant with fins |
US5755810A (en) * | 1996-11-13 | 1998-05-26 | Cunningham; Robert A. | Hip implant prosthesis |
US6168627B1 (en) | 1998-03-17 | 2001-01-02 | Acumed, Inc. | Shoulder prosthesis |
US6193758B1 (en) | 1998-03-17 | 2001-02-27 | Acumed, Inc. | Shoulder prosthesis |
US6168628B1 (en) | 1998-03-17 | 2001-01-02 | Acumed, Inc. | Shoulder Prosthesis |
US6102953A (en) * | 1998-03-17 | 2000-08-15 | Acumed, Inc. | Shoulder prosthesis |
US6494913B1 (en) | 1998-03-17 | 2002-12-17 | Acumed, Inc. | Shoulder prosthesis |
US20110196491A1 (en) * | 1998-03-17 | 2011-08-11 | Acumed Llc | Bone prosthesis |
US7918892B2 (en) | 1998-03-17 | 2011-04-05 | Acumed Llc | Shoulder prosthesis |
US5961555A (en) * | 1998-03-17 | 1999-10-05 | Huebner; Randall J. | Modular shoulder prosthesis |
US20080306600A1 (en) * | 1998-03-17 | 2008-12-11 | Huebner Randall J | Shoulder prosthesis |
US7297163B2 (en) | 1998-03-17 | 2007-11-20 | Acumed Llc | Shoulder prosthesis |
US20100312349A1 (en) * | 2000-04-10 | 2010-12-09 | Biomet Manufacturing Corp. | Modular prosthesis and use thereof for replacing a radial head |
US8114163B2 (en) | 2000-04-10 | 2012-02-14 | Biomet Manufacturing Corp. | Method and apparatus for adjusting height and angle for a radial head |
US9579208B2 (en) | 2000-04-10 | 2017-02-28 | Biomet Manufacturing, Llc | Modular radial head prosthesis |
US9439784B2 (en) | 2000-04-10 | 2016-09-13 | Biomet Manufacturing, Llc | Modular radial head prosthesis |
US9333084B2 (en) | 2000-04-10 | 2016-05-10 | Biomet Manufacturing, Llc | Modular prosthesis and use thereof for replacing a radial head |
US8920509B2 (en) | 2000-04-10 | 2014-12-30 | Biomet Manufacturing, Llc | Modular radial head prosthesis |
US8535382B2 (en) | 2000-04-10 | 2013-09-17 | Biomet Manufacturing, Llc | Modular radial head prostheses |
US8425615B2 (en) | 2000-04-10 | 2013-04-23 | Biomet Manufacturing Corp. | Method and apparatus for adjusting height and angle for a radial head |
US8366781B2 (en) | 2000-04-10 | 2013-02-05 | Biomet Manufacturing Corp. | Modular prosthesis and use thereof for replacing a radial head |
US20110125276A1 (en) * | 2000-04-10 | 2011-05-26 | Biomet Manufacturing Corp. | Modular prosthesis and use thereof for replacing a radial head |
US20100030339A1 (en) * | 2000-04-10 | 2010-02-04 | Biomet Manufacturing Corp. | Method and apparatus for adjusting height and angle for a radial head |
US8110005B2 (en) | 2000-04-10 | 2012-02-07 | Biomet Manufacturing Corp. | Modular prosthesis and use thereof for replacing a radial head |
US20050075735A1 (en) * | 2000-04-10 | 2005-04-07 | Berelsman Brian K. | Method and apparatus for adjusting height and angle for a radial head |
US20110144759A1 (en) * | 2000-04-10 | 2011-06-16 | Biomet Manufacturing Corp. | Modular prosthesis and use thereof for replacing a radial head |
US20100241236A1 (en) * | 2000-04-10 | 2010-09-23 | Biomet Manufacturing Corp. | Modular Radial Head Prosthesis |
US20100262252A1 (en) * | 2000-04-10 | 2010-10-14 | Biomet Manufacturing Corp. | Modular prosthesis and use thereof for replacing a radial head |
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Also Published As
Publication number | Publication date |
---|---|
EP0131178B1 (de) | 1988-11-02 |
EP0131178A2 (de) | 1985-01-16 |
DE3474906D1 (en) | 1988-12-08 |
ATE38320T1 (de) | 1988-11-15 |
DE3323131A1 (de) | 1985-01-03 |
EP0131178A3 (en) | 1986-12-03 |
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